Apparatus and method for locating an interventional medical device with a ultrasound color imaging system

ABSTRACT

A VIBER vibrating mechanism is coupled to a cannula or needle and operates to provide flexural vibrations to move the needle and to enable detection of the position of a needle within a body of interest by a color ultrasound imaging system. The VIBER mechanism exhibits multiple modes of oscillation when energized. The VIBER mechanism is excited to exhibit predetermined oscillations at a given frequency in the X plane, a predetermined oscillation at another frequency in the Y plane and still another frequency of oscillation in the Z plane. In this manner, the VIBER mechanism device exhibits motion in all three planes, which motion is detectable by a conventional color ultrasound imaging system. The frequency of oscillation is a function of the entire system, namely the VIBER mechanism, the needle or cannula which is attached to the VIBER mechanism and the tissue. The resonant frequency is preferred as it provides larger vibrational amplitudes. In this manner, a resonant frequency is controlled by means of a feedback control loop, whereby the frequency applied to the VIBER mechanism is monitored to determine resonance and is held at the resonant frequency as the VIBER mechanism or needle is moved. The vibration in the representative planes causes a typical conventional color ultrasound imaging system to display the vibration or movement by means of a color variation. By viewing the display, a system operator, such as a physician can visualize the location of the needle because of the color indication provided by the display.

This is a division of application Ser. No. 08/022,112, filed Feb. 25,1993.

FIELD OF THE INVENTION

The present invention relates to ultrasound imaging systems and moreparticularly, to the detection and display of the location of aninterventional medical device by a color ultrasonic imaging systemthrough detection of motion causing a Doppler shift.

BACKGROUND OF THE INVENTION

As is well known in the medical profession, ultrasonic imaging isutilized to enable a physician to view an internal area of a patient'sbody that is of concern to the physician. For example, ultrasonicimaging is utilized in procedures such as the biopsy of possiblymalignant tumors, and so on. In a biopsy procedure, an interventionalmedical device, such as a biopsy needle, is inserted into the patientand moved to the internal area imaged by an ultrasonic imaging system.It is an objective during such procedures for the physician to clearlyvisualize the needle and therefore monitor the movement of the needlethrough the body as it approaches the tissue masses for removal by thebiopsy needle.

There are various approaches, employing various means, to enable a userto view the movement of a needle, as it is guided through a patient'sbody or otherwise. Particular reference is made to U.S. Pat. No.5,095,910 entitled ULTRASONIC IMAGING 0F BIOPSY NEEDLE issued on Mar.17, 1992 to Jeffry E. Powers (the '910 patent). This patent describes asystem for imaging a biopsy needle with ultrasound, wherein the needlecauses a Doppler response in a color ultrasonic imaging system throughcontrolled, highly directional motion produced by the reciprocation ofthe needle tip. The '910 patent describes a biopsy needle which includesa hollow cannula that carries a removable stylet. There are shown meansfor reciprocating the stylet which is coupled to the proximal end of thestylet and the distal tip of the stylet is reciprocated at the distalend of the cannula. This motion is a reciprocal motion that is detectedthrough Doppler interrogation of the transducer on the catheter duringultrasonic scanning modes can be ascertained and incorporated into theimage generated by the imaging system. As in the case of the systemdescribed in the '910 patent, only one point of the medical device isdetected and displayed.

The color ultrasound imaging described in the '910 patent is arelatively new form of ultrasound imaging. Reference is also made to anarticle entitled "Medical Ultrasonic Imaging--State of The Art andFuture", Electro-International Conference Record, Region 1, Central NewEngland Council, METSAC, IEEE and New England and New York Chapters,ERA, Apr. 16-18, 1991, pp. 64-65 by Vilkomerson, D., Gardineer, B., andLyons, D for background information on color ultrasound imaging.

Color imaging has also been utilized in ultrasound systems used tomeasure blood velocity. The prior art recognizes that moving blood cellsreflect ultrasonic energy that is Doppler shifted in frequency.Therefore, the velocity of the blood may be measured by utilizing anultrasound imaging system. Moreover, ultrasound imaging systems havebeen utilized to locate the best point in a blood vessel in which tomeasure blood velocity by measurement of the Doppler shift. The Dopplershift in back-scattered ultrasound at a point in a blood vessel ismeasured by the detection of quadrature time samples of theback-scattered signal. This technique entails the monodyne detection ofthe signal in conjunction with sine and cosine mixing at a transmittedfrequency in order to detect real and imaginary parts of a signal vectorat a sampling time. The signal vector, which is a sum of the individualsignal vectors from each blood cell, changes slowly (assuming the bloodcells stay in the same relative positions) but advances or retreats inphase depending upon whether the blood cells are coming toward atransducer or away.

FIG. 1 (prior art) shows the result of two measurements in time of asignal vector 20. If the signal vector 20 is obtained at time t₁, andafter a time t the signal vector 20 is obtained from the same bloodsample at time t₂, the signal vector 20 will have advanced, in acounterclockwise direction, from θ(t₁) to θ(t₂). Continued measurementsof the signal vector show that the signal vector rotates at a ratef_(d), which can be shown to be a Doppler frequency as calculated by astandard physics formula. The Doppler frequency or frequencies can thenbe analyzed by a spectrum analyzer in order to show the distribution ofblood velocities as a function of time. However, Doppler informationover the entire image frame is not provided with this technique.Furthermore, the Doppler ultrasound signal path is independent of theimage ultrasound signal path.

In order to overcome these deficiencies, the prior art noted that themeasurements depicted in FIG. 1 are enough to determine the bloodvelocity. The phase shift shown in FIG. 1 is proportional to thedistance in wavelengths that the blood cells have moved. In addition,since the time interval between measurements is known, dividing thedistance that the blood vessels have moved by the time interval betweenmeasurements yields the blood velocity. Since two samples at a point ina blood vessel were sufficient to calculate blood velocity, imagingpulses are then employed to determine blood velocity. Therefore, thevelocity of the blood cells could be determined at every point in theultrasonic image display. Furthermore, in the known blood velocitysystem, the velocity of the blood cells is provided on an image displaywith the pixels in the image display colored as a function of thevelocity of the blood cells at every point. :

Color ultrasound imaging systems are sensitive to the relatively smallmotion of blood in arteries, to displacements measured in microns.Typical state of the art systems are able to show velocity in the 1 to100 centimeters per second (cm/sec) or more range on a color imagedisplay. In order to accomplish this, the first and second imagingpulses are produced every 80 to 330 microseconds (μsec) depending on thescale of the velocity to be detected. If a 5 cm/sec velocity is detectedwhere the sampling interval of the imaging pulses is 118/μsec, thedisplacement of the point is 5 cm/sec times 118/μsec, or approximately 6microns. Therefore, small vibratory motions, on the order of microns,are detectable by color flow imaging.

Furthermore, there are commercially available needles with grooved tips,(e.g., the Echotip from W. Cook and Co.), to reflect ultrasound betterto attempt to make the needles more visible in an ultrasound image.

In terms of additional background, some years ago physicians noticedcolor images appearing when needles were advanced through tissue(McNamara, M. P., AJR 152, p. 1123 (1989), Kurohiji et al., J.Ultrasound Med 9: pp. 243-245, 1990). Kimme-Smith et al., in a papergiven at the AIUM, in February 1991 (see abstract in Journal ofUltrasound in Medicine, Volume 10, Number 3, p. 64) described making aneedle visible on a colorflow imaging system by using a 400 Hz buzzer,an extension of the previous observations. The impression given in theKimme-Smith article is that the buzzer acts in a reciprocating motion inthe same manner as is done by hand, although the article is not clear onwhat exactly was done. The authors do not report consistentvisualization using their method.

SUMMARY OF THE INVENTION

The present invention is directed to a method and apparatus for causinga periodic or oscillating mechanical motion in an interventional medicaldevice. The oscillatory nature of the mechanical motion results in asignificant Doppler shift effect that is readily detected by a colorultrasonic imaging system to provide a clear color image of the devicewithin the area of a patient scanned and displayed by the imagingsystem. The present invention utilizes the sensitivity of known colorultrasonic imaging systems to micron sized vibrations as a basis forproviding a detectable presence of an interventional device for imagingthe device. Micron sized oscillatory distortions permit a colorultrasonic imaging device to detect and display a colored image of thedevice within a grayscale image of surrounding tissue.

Generally, the present invention comprises a mechanical motion mechanismcontrollably activated to periodically move through preselectedmechanical positions. A mechanical coupling element is mounted on themechanical motion mechanism and coupled to an interventional device fortransmitting mechanical energy generated by the periodic motions as anoscillating force to the interventional device. Pursuant to the presentinvention, the preselected mechanical positions and oscillatory natureof the motions are arranged and configured to transmit the mechanicalenergy produced by the periodic motions via the coupling element asflexural waves that propagate along the length of the interventionaldevice.

Flexural waves are a known form of vibrational motion that occurs inrod-like elements under certain circumstances. Rod-like elements are atypical configuration for interventional medical devices such as, e.g.,needles and guidewires. Flexural waves exhibit characteristics similarto standing or propagating waves. For example, the mechanical motiontransmitted to the interventional medical device can be controlled tocause micron sized mechanical distortions along the entire length of thedevice that exhibit a sinusoidal wave shape. The sinusoidal wave shapecauses a series of Doppler shifts along the length of the transmittedflexural wave as a function of the periodically changing peaks andvalleys of the sinusoidal wave shape.

Moveover, the mechanical motion mechanism can be controlled to transmitthe mechanical motions in specific axial modes so that, e.g., theflexural waves propagate along one or more specific axes of the rod-likeshape of the interventional device. Thus, the mechanical motionmechanism can be configured and controlled to cause flexural waves topropagate along one or more of the X, Y and Z axes of the device. Inaddition, highly efficient flexural wave generation along preselectedaxes of the device can be achieved by fixing the period of themechanical motions that cause the flexural waves, to correspond to oneor more resonant frequencies of the interventional device when it iscoupled to the mechanical motion mechanism and inserted into a patient'sbody.

The mechanical motion mechanism can be utilized to assume periodicpositions that result in flexural wave transmission along one or morepreselected axes when the mechanism is activated by driving forces setat one or more of the resonant frequencies of the interventional device.In addition, the driving forces can be effectively controlled byconventional feedback techniques to maintain the desired operation atthe resonant frequencies.

The present invention recognizes that mechanical distortions of aninterventional device that assume the form of flexural waves provide aseries of Doppler shifts along the propagated flexural wave shape thatare readily detected by highly sensitive color ultrasound imagingsystems for improved imaging of the entire interventional device when itis within a body. In addition, by transmitting the flexural waves inaxial modes under resonant frequency operation, a scanner of theultrasound color imaging system can be exposed to Doppler shiftsemanating from each of, e.g., X, Y and Z axial directions. Accordingly,the orientation between the interventional device and the scanner is notcritical to the detection and accurate display of the interventionaldevice. Moreover, the axial modes permit the inherent resonance of thedevice to be utilized for efficient axial mode operation resulting fromwave generation at resonant frequencies.

It has also been observed that flexural waves of a particular axial modedo, to some extent, migrate beyond the axis of propagation. Thus,Doppler shifts are provided from positions of the interventional devicethat extend beyond the specific X, Y and Z axial positions. Themigration phenomenon expands the detectability of the interventionaldevice while maintaining the efficiency afforded by causing mechanicaldistortions via flexural waves transmitted during resonant frequencyactivation. The efficiency of operation is further enhanced by takingadvantage of the micron sized distortion sensitivity of known colorultrasound imaging system. The undulations of the flexural wavestransmitted to the interventional device need only be of a few micronsin magnitude to permit high quality detection of Doppler shifts alongthe entire length of a device. The detected Doppler shifts can be usedto generate and display a color image of the entire device within thegrayscale image of surrounding tissues.

BRIEF DESCRIPTION OF THE FIGURES

FIG. 1 is a graphical representation depicting measurements in time oftwo signal vectors and useful in describing the operation of the presentinvention.

FIG. 2 is a pictorial representation of an ultrasound imaging system fortransmitting mechanical motion to a cannula or other element accordingto the present invention;

FIG. 3 is a planar representation of a mechanical motion mechanismcoupled to a needle according to the present invention;

FIG. 4 consists of FIGS. 4a, 4b and 4c showing various resonantfrequency modes which are accommodated by the flexural wave preparationaccording to the present invention.

FIG. 5 comprises a series of figures, namely 5a, 5b, 5c and 5d depictingvarious drive systems to excite the mechanical motion mechanismillustrated in FIG. 3.

FIG. 6 is a graph depicting voltage vs. frequency response useful indescribing the present invention.

FIG. 7 is a block diagram showing a feedback based frequency controltechnique for supplying a drive voltage to the mechanical motionmechanism illustrated in FIG. 3.

FIG. 8 is a series of diagrams including FIGS. 8a, 8b and 8c depictingvarious drive and sense mechanisms which can be employed in the feedbackscheme depicted in FIG. 7.

DETAILED DESCRIPTION

As discussed above, FIG. 1 depicts relationships showing how bloodvelocity is measured in typical ultrasound systems. As is well known,such measurements can also be performed to detect the reciprocatingmotion or other motion of an interventional device such as a needle.Referring to FIG. 2, there is shown a simple block diagramrepresentative of the operation of an exemplary embodiment of thepresent invention. FIG. 2 depicts an ultrasound imaging scan head 22that is coupled to an ultrasound imaging system 24 having a display 25.The scan head 22 is shown impressing an imaging pulse 26 on a point of avibrating element 30 such as an interventional device (displacement ofthe vibrating element 30 via phantom lines is exaggerated for clarity).The interventional device can be, e.g., a needle. As an example ofoperation, the point 28 may be closest to the scan head 22 when thefirst imaging pulse 26 occurs and furthest when the second imaging pulseoccurs. Known imaging systems 24 are able to detect and display thevelocity of a moving element in the 1-100 centimeters per second or more(cm/sec) range. In order to accomplish this, the first and secondimaging pulses 26 of FIG. 2 are produced typically every 80 to 330microseconds (μsec) depending on the scale of the velocity to bedetected. If a 5 cm/sec velocity is detected with a sampling interval ofthe imaging pulses set at 118 microseconds, the detected displacement ofthe point 28 is 5 centimeters/second times 118 microseconds, orapproximately 6 microns. Therefore, as indicated above, small vibratorymotions, on the order of microns, can be detected by known colorflowimaging systems.

As will be explained and referring to FIG. 2, a mechanical motionmechanism 31 according to the present invention is coupled to the needle30. The mechanical motion mechanism 31 is capable of operating in atleast one of a multiplicity of mechanical motion modes including modesable to transmit mechanical energy along one or more of the X,Y and Zaxes of a device. According to the present invention, the mechanicalenergy produced by the mechanical motion mechanism 31 causes thetransmission of mechanical energy in the form of flexural waves to theneedle 30. As a result, the needle 30 undulates in flexural modes asdepicted in FIG. 2 between the solid and phantom lines. In this manner,the needle 30 exhibits flexural vibrations in the X,Y and/or Z planes.Accordingly, the ultrasonic imaging system 24, via the scanner 22, candetect Doppler movements resulting from undulations of the flexuralwaves in any of the X, Y and Z planes and provide a precise indicationon the display 25 as to the location of the needle 30 within a patient.To the contrary, as noted above in prior art techniques, the motion of aneedle, to be detected and displayed, is a highly directionalreciprocating motion along a longitudinal axis of the needle. Dependingon how the scanning head is oriented relative to the needle, thereciprocating of the needle may entirely be missed or confused so thatthe practitioner will not know the exact positioning of the needle inrelation to the body of the patient.

As indicated and as will be explained in conjunction with FIG. 3, themechanical motion mechanism 31 operates in unique oscillatory modes togenerate and transmit flexural waves along the needle 30. The termflexure as noted above, is utilized to denote the curving or bent stateof the needle which is produced by the wave-like characteristics of themechanical energy transmission generated by the mechanical motionmechanism 31. Flexure occurs in an elastic structural material when adeflection is suitable to set-up stresses in the material. The flexuralwaves are vibratory flexural waves which may operate and exhibitcharacteristics similar to standing waves or as propagating waves. Theflexural waves provided by the mechanical motion generation are in oneexemplary embodiment, transmitted about or along the X,Y and/or Z axesat synchronized, but nonharmonically related frequencies that correspondto resonant frequencies of the needle 30, as will further be explained.

Referring now to FIG. 3, there is shown a needle or cannula 41 which isassociated with a hub 42. The needle 41 is directed through and coupledto a mechanical motion mechanism according to an exemplary embodiment ofthe present invention and designated generally by the reference numeral40. The mechanism 40 is constructed from a suitable metal material suchas brass, zinc, stainless steel and alloys of the same. The term "VIBER"is a coined term used as a trademark by Echo Cath, Inc., the assigneeherein, and is used to describe the vibratory mechanism 40. As one canascertain, the mechanism 40 is formed to a generally C-shapedconfiguration having an elongated peripheral slot 44 which is bounded onone side by a pendulum-shaped member 45 and on the other side by asection 46 arranged to mount one or more plate-shaped piezocrystaldiaphragms 48. At least one of the piezocrystal diaphragms 48 isactivated or excited by means of a suitable voltage source as will beexplained. For example, a metal electrode plate 49 can be utilized tocouple the illustrated piezocrystal diaphragm 48 to a source of voltage.

As illustrated in FIG. 3 and FIG. 4, the VIBER mechanism 40 comprised isa generally cylindrical or annular member having an internal hollowsection of a relatively complex configuration designed to undergovarious preselected motions, as will appear. The slot 44, as seen forexample in FIG. 4, extends into the center of the annular shaped VIBERmechanism 40 towards a bottom curved surface. The slot is bounded on oneside by the pendulum-shaped member 45 that includes a reduced neckportion and an end portion comprising a larger mass relative to the neckportion. The end portion of the pendulum-shaped member 45 together withthe neck portion forms a pendulum like structure. As shown both in FIG.3 and FIG. 4, there is also a downwardly extending depending wall 65which serves to protect the piezocrystal diaphragm 48. The piezocrystaldiaphragm 48 may be integrally formed with the VIBER mechanism 40 or maybe a separate diaphragm, such as unimorph ceramic slab tightly coupledto the VIBER mechanism 40 by epoxy, glue, etc., and/or held in place byspringing open the VIBER mechanism 40 and inserting the diaphragm 48 andthereafter allowing the frame to relax thereby tightly gripping thediaphragm 48 when the mechanism 40 returns to its relaxed position. Themetal electrode plate 49 is coupled to the piezocrystal diaphragm 48 byglue, epoxy, welding and other suitable manner, but is offset from thecenter of the diaphragm 48.

A spring-like clip 43 is mounted to the pendulum-shaped member 45, asillustrated in FIG. 3. The clip 43 is used to secure the needle orcannula 41 to the VIBER mechanism 40. One of the advantages of the VIBERmechanism 40 is that it can be affixed to an any type of needle 41. Aslong as the means of affixing the needle is flexible, such as a springwire metal clip 43, different needle gages can be secured by the clip43. Current medical practices utilize needles of gages from 16 (1.6 mmdiameter) to 25 (0.4 mm diameter) and of lengths from 0.5 inches to 10inches, and also of many different style cutting tips. It isadvantageous to provide a mechanism that is suitable for use with avariety of needles of different sizes and lengths. The VIBER mechanism40, with its flexible clip 43, can be coupled to any particular needleeven after the needle has been inserted into the body if visualizationis then required. As one can see from FIG. 3, the diameter of the VIBERmechanism 40 is slightly larger than the diameter of the needle hub 42.It may be twice the diameter and so on, but in any event, it is designedas a relatively small and compact unit for convenient use during aninterventional procedure. The circular outer peripheral surface of theVIBER mechanism 40 enables convenient manipulation of the combinedmechanism/needle structure when directing the same through the interiorof a body.

As indicated above, the VIBER mechanism 40 exhibits complex vibratorymotion and essentially provides vibratory oscillations in the differentplanes (X,Y & Z). As will be explained, the VIBER mechanism 40 isvibrated by excitation of the plate-shaped piezocrystal diaphragm 48resulting in the transmission of flexural waves to the coupled needle 41via the clip 43. For example, a voltage of a preselected frequency canbe applied to the piezocrystal 48 via electrodes such as the metalelectrode plate 49. Due to the inherent properties or piezocrystalmaterials, the applied voltage causes the crystal to undergo mechanicalvibrations as a function of the amplitude and frequency of the appliedvoltage. The mechanical vibrations or the piezocrystal diaphragm 48periodically distort the shape of the VIBER mechanism 40 through variouspositions, also as a function of the amplitude and frequency of theapplied voltage, resulting in the transmission of mechanical energy fromthe VIBER mechanism 40 to the needle 41, via the clip 43.

The VIBER mechanism 40 is designed to exhibit complex vibratory motionsdue to mechanical vibrations of the piezocrystal diaphragm 48 tocontrollably provide undulating oscillations at the clip 43 in differentplanes (e.g., X, Y & Z planes).

Experience indicates that the best color images are obtained atvibratory frequencies of 2/3 of ultrasound pulse repetition frequency,which for most commercial medical ultrasound instruments is indicativeof vibratory frequencies of between 0.2 and 10 KHz. The mechanicalresonance of the VIBER mechanism 40 amplifies the mechanical vibrationsproduced by the excited piezocrystal diaphragm 48, just as largeexcursions of a "swing" are the amplified effect of small pushes at theresonant rate of the swing. By operating the mechanism 40 at a resonantfrequency of the mechanism 40 and attached needle 41, relatively smallforces from the piezocrystal diaphragm 48 can be used to provideflexural wave transmissions to the needle 41 that result in mechanicalmotion of the needle 41 of sufficient magnitude for detection by knowncolor ultrasonic imaging systems. It is indicated that whilenon-resonant operation of the VIBER mechanism 40 may also be used, suchnon-resonant operation does require stronger drive elements.

Referring now to FIG. 4, there is shown three views, namely 4a, 4b and4c of the VIBER mechanism 40 as shown in FIG. 3, depicting threedifferent modes of oscillations. In FIG. 4, there are various shadesemployed to illustrate the degree of movement of each of the shadedareas. Referring to FIG. 4a, there is shown a front plan view of theVIBER mechanism 40 including a small replica of an X, Y and Z set ofaxes in the center of the diagram. The left hand bottom of the VIBERmechanism 40 is characterized by an extending circular arm 50 having areduced neck portion 51 which extends to and terminates in thependulum-like member 45 with the relatively large bottom mass. Thependulum analogy is made based on the thinner neck portion with therelatively larger end portion. The member 45 is of a generally "L" shapecross-section used to reinforce oscillations caused by periodicdistortion of the piezocrystal diaphragm 48, as described above.

As seen in FIG. 4a, there are a series of arrows associated with variousregions along the pendulum-like member 45. The regions are depicted bythe reference numerals 55, 56, 57, 58 and 59. Each region is depicted ina different shade with each shade being indicative of the extent ofmovement of one region with respect to other regions. The firstoperating mode, which is the lowest frequency of activation of thepiezocrystal diaphragm 48 for the dimensions and material of theexemplary VIBER mechanism 40 depicted in FIG. 4a, is at 860 Hz. 860 Hzis a resonant frequency for the exemplary VIBER mechanism 40. In thismode, the pendulum-like member 45 is caused to oscillate by the 860 Hzdistortion of the piezocrystal diaphragm 48 in the direction of thearrows, as from left to right and right to left, along the X axis. Theamount of motion is a function of the shading whereby region 55 movesthe most, region 56 moves more than region 57 which moves more thanregion 58, with region 59 which is analogous to the main massconcentration moving very little compared to the other regions. In asmuch as the clip 43 is mounted to the lower portion of the pendulum-likemember 45, the oscillating motion along the X axis is transmitted to theneedle 41 secured by the clip 43. The activating voltage applied to thepiezocrystal diaphragm 48 at the resonant frequency of 860 Hz issufficient to cause the X axis oscillation of the pendulum-like member45 to transmit waves along the X axis of the needle 41.

In FIG. 4b, the resonant frequency of oscillation is 1305 Hz and thedirection of the arrows again indicates the movement of the variousshaded regions of the VIBER mechanism 40. As one can see, the movementdepicted in FIG. 4b is mainly along the Y axis and the member 45 ismoving up and down in the vertical plane or transverse to the X axismovement shown in FIG. 4a. The greatest movement occurs in region 60with lesser movement in region 61 as shown in FIG. 4b.

Referring to FIG. 4c, there is shown the third oscillatory mode at aresonant frequency of 2840 Hz which basically is occurring about the Yaxis or in directions of the Z axis. In the exemplary embodiment, thedirections of the arrows indicate the relative movement which is atorque or twisting movement in and out of the plane of the paper. Inthis mode, the left side of the device is moving up and down (Y axis)and is also twisting in and out of the plane (Z axis) of the paper.

As should be understood, all of these modes can be achieved by drivingthe diaphragm 48 at an appropriate frequency. The frequency applied todiaphragm 48 need not be related to the oscillatory frequencies of FIG.4a-4c. As indicated, these frequencies typically vary for ultrasoundsystems between 0.2 and 10 KHz. It is of course understood that thereare other geometric forms which can be employed for the VIBER mechanism40 so long as oscillating motions can be generated along preselectedaxis, as, e.g., the X, Y and Z areas of the structure used for themechanical motion VIBER mechanism 40. The exemplary circular shape ofthe mechanism shown in FIG. 4a allows for easy mechanical machining andimplementation. The device can also be changed in frequency modes bymachining or changing the shape of the member 45 and thus obtainingdifferent resonant frequencies.

The vibratory modes as depicted in FIGS. 4a, 4b and 4c can be generatedsimultaneously. Thus, based on these vibrational modes, the ultrasoundimaging system can now detect Doppler changes in the X,Y and Z planes orin all planes which result in a marking on the display indicative of theexact location of the needle 41 receiving flexural waves from the VIBERmechanism 40. The dominant motion of any flexural wave may be along oneaxis perpendicular to the axis of the member which is carrying theflexural wave. Flexural waves will be produced at the ends of thestructure such as next to the hub 42 of the needle or at bends in thestructure where the bending moment of the flexural wave will have acomponent in the orthogonal axis, if it is desired that thispolarization of the flexural wave be minimized, e.g., so that thephysician does not need to worry about the rotational orientation of theVIBER mechanism 40 on the needle. Thus, one can excite different modesof resonance for the VIBER mechanism 40 whose dominant motions are onthe orthogonal axes.

The modes depicted in FIG. 4 can be either sequentially orsimultaneously excited to produce motions along all axes (X,Y and Z) ofthe flexural wave carrying needle 41. In any event, the twist mode asdepicted in FIG. 4c may be used to affect both motions. It is of courseunderstood that if these modes are implemented sequentially, it shouldbe realized that the period of excitation of each mode should be longenough to build up the resonance of that mode, as for exampleapproximately Q÷π vibratory cycles, where Q is the measure of the ratioof the stored energy to the dissipated energy of a resonant structure.The concept of Q of course is well known in regard to vibratory modes.

Referring now to FIG. 5, there is shown several exemplary drive circuitsfor activating the piezocrystal diaphragm 48 of the VIBER mechanism 40.FIG. 5a depicts a bimorph piezoceramic crystal element for the diaphragm48. As seen, the piezoceramic element is connected to a voltage source69 and is excited at a particular frequency. As indicated, the frequencyof excitation of the piezoceramic will cause the VIBER mechanism 40 toproduce multiple modes of oscillation along the X,Y and Z axes. Thefrequencies are all synchronized even though they are not harmonicallyrelated. Piezoelectric devices to produce mechanical resonance are wellknown and many examples of such devices exist in the prior art.

In this manner FIG. 5b depicts a piezoceramic or piezoelectric device 48which is a unimorph device which again is activated by means of anoscillator circuit 80. The unimorph device 71 may be coupled to asuitable membrane or wall which may be constructed from brass or othermaterials to couple the vibratory modes of the piezoceramic device tothe VIBER mechanism 40 or may be a simple slab piezoceramic driver thatextends and contracts along its long axis when supplied with a varyingvoltage. As one can ascertain, piezoelectric ceramic devices such asceramic unimorphs are used for both transmitters and receivers intelecommunication systems. The piezoelectric activity owes to anelectrically polarized, synthetic ferroelectric ceramic. The flexuralneutral axis of the composite structure is not at the ceramic'smidplane; thus, vibration results in variation of the ceramic's diameterwhich induces a voltage across its thickness as defined through thepiezoelectric constant. Such devices, as indicated, are well known, asis the entire field of piezoelectric transduction. In any event, suchtransducers are optimum devices to generate the frequencies required forexcitation of the VIBER mechanism 40.

Referring to FIG. 5c, diaphragm 48 comprises a transducer 72 which, inturn, comprises a magnetic transducer. Such a magnetic transducer canagain be energized or excited by means of an oscillator 81 to oscillateat the above-described frequencies.

Referring to FIG. 5d, there is shown a diaphragm 48 that comprises atransducer 78 which uses a magnetostrictive effect. The transducer isexcited by means of an oscillator 82. Magnetostrictive devices are alsowell known devices. Generally, magnetostrictive materials offer certainadvantages for certain transducer applications.

Such devices, as well as piezoelectric ceramic materials have beenutilized for underwater sound transducers. In case of piezoceramictransducers they are usually modified lead zirconate titanate (PZT)compositions and to a lesser extent modified barium titanatecompositions. In the case of magnetostrictive materials, such materialsemploy nickel, Alfenol, Ferroxcube, Terfonal and other materials aswell. The use of such materials is, as indicated, well known and commonproperties of such materials are well documented.

Another mode of operation of such a VIBER mechanism is that of pulsedexcitation (FIG. 2), where the rate of the vibrating frequencies isseveral times of that of the frame rate of the scanner of the ultrasonicimaging system (which are typically 4 to 12 frames per second). Thisoperation produces beads of color on the flexural wave carryingintervention device. These pulses of excitation must be wide enough tobuild up the resonance as above-described.

While the exemplary VIBER mechanism 40 has particular resonantfrequencies determined by the shape of the mechanism and characteristicsof the materials used to fabricate the mechanism, once the needle isaffixed to the structure and placed in tissue, the resonant frequency ischanged. As seen in FIG. 3, the needle 41 once coupled by the metal clip43 to the VIBER mechanism 40 now produces a change in resonancefrequency of the system due to a change in structure and mass. Thechange is relatively small as long as the needle mass is much less thanthat of the VIBER mechanism mass. This is normally the case. The VIBERmechanism 40 may be constructed from a suitable metal such as brass orstainless steel. The needle which may be stainless steel is an extremelythin tube or cannula with a very light needle hub 42. Thus, the mass ofthe VIBER mechanism 40 is much greater than the mass of the needle. Inany event, the amount of the resonant frequency shift depends upon themass, diameter and length of the needle and also upon thecharacteristics of the tissue in which the needle is inserted. Aresonant mode is preferred for the system to obtain maximum amplitudevibrations. While the system can be tuned manually, it is of advantageto have a self adjusting system to automatically drive the VIBERmechanism member 40 with the optimal frequency and always near or atresonance.

Referring to FIG. 6, there is shown a typical example of voltage vs.frequency depicting a resonant frequency at f_(o) which ischaracteristic of a dip which occurs in the driving waveform when aresonant frequency is achieved. This dip in voltage can be utilized ordetected to determine the particular resonant frequency of the combinedstructure which includes the VIBER mechanism 40 and the needle orinterventional medical device 41, as shown in FIG. 3. This dip involtage is due to the back voltage generated by the motion of thestructure. In the case of structures that utilize a piezoelectric platewhen the VIBER mechanism 40 moves, a bucking voltage is generated by thepiezoelectric effect. Similarly, when a magnetically driven structure isat resonance, the moving pole pieces will induce a back EMF in the coilthat will cause a reduction in the voltage. In general, at resonance,the driving characteristics change. Thus, as one can ascertain, bymonitoring the driving waveform as the frequency varies, resonance canbe detected.

Referring to FIG. 7, there is shown a circuit which operates to detectresonance and operates to automatically maintain the frequency used todrive the VIBER mechanism 40 system at resonance. As seen the VIBERmechanism 40 is shown with the clip 43 secured thereto and which clip isaccommodating a needle as for example needle 41 of FIG. 3. In any event,there is shown a transducer drive element 48 which for example may be apiezoelectric ceramic device as shown for example in FIGS. 5a and 5b.The element 48 is coupled to a variable frequency generator 92 that cangenerate frequencies in the range between 2 to 10 KHz depending upon themedical ultrasound instruments being used. Within the above describedfrequency range, the variable generator 92 may produce a frequency rangeof between 2-3 KHz or between 9-10 KHz and again as a function of theparticular ultrasound imaging system that is being employed. Asindicated, most commercial medical ultrasound instruments contain meansto detect vibratory frequencies between the above-described limits of 2and 10 KHz.

The variable generator 92 provides a range of frequencies to the VIBERmechanism 40 by means of the piezoelectric or magnetic transducer 48.The drive leads as shown are coupled to the input of an analog todigital converter 90 which converts the analog drive voltage to digitalsignals at its output. The digital output is applied to the input of aCPU 91 or processor. The CPU 91 includes a microprocessor which analyzesthe magnitude of the digital signals applied as the waveform of theoscillator 92 is varied. The oscillator 92 is varied by means of acontrol voltage which is applied by the processor 91 to a controlterminal of the oscillator 92 to vary the frequency. The processor 91analyzes the magnitude of the drive waveform as the oscillator 92frequency is varied. In any event, by conventional feedback techniques,the oscillator frequency or the frequency utilized for driving theelement 48 is forced to be at the frequency of resonance of the system.The resonant frequency is the entire resonant frequency of the systemwhich includes the VIBER mechanism 40, the needle and the body tissue.

While the technique as shown in FIG. 7 provides operation that isreliable, there are other ways of controlling the frequency of themechanism. Where there is a large dip in the drive waveform and wherethere is low noise in the measured waveform, in some situations aseparate sensing element can be employed as part of the resonantstructure.

Referring to FIG. 8, there is shown various alternate devices where aseparate sensing element is formed as part of the resonant circuit. InFIG. 8a, a sensing piezoelectric element is formed adjacent to the drivepiezoelectric element. The sensing element depicted by reference numeral105 is formed by conventional techniques and is located adjacent thedrive element 106. In this manner, as the drive element receives drivingvoltages, the sensing element is energized by means of these drivingvoltages and enables a separate output to be provided. Thus, a separatepiezoelectric element or alternatively a separate electrode on thedriving piezoelectric plate will produce a characteristic change involtage whose amplitude is related to the amount of motion and is amaximum at resonance. The peak in such a signal which is present in theoutput of the sense piezoelectric element 105 can easily be detectedutilizing the feedback scheme as shown in FIG. 7. In these cases, theoutput of the sensing device is applied to the input of the A/Dconverter.

In FIG. 8b, there is shown a separate drive and sense coils which areassociated which a magnetic drive circuit such as those shown in FIGS.5c and 5d. In this manner, the drive coil 100 receives a drive voltagefrom the variable generator 92 of FIG. 7, while the sense coil detectsand applies the voltage to the input of the A/D converter 90.

In FIG. 8c, there is shown a separate drive element 102 which may be apiezoelectric or other type of drive with a separate layer which is aPVF2 film 103 applied to the outer peripheral area of the VIBERmechanism 40. The film 103 operates as a sensing element with electrodesapplied directly to the A/D converter 90 of FIG. 7. It is of courseshown that with such sensors, as depicted in FIG. 8, it is also easy tomeasure and to display the amount of motion to be applied to the needleor other device to indicate to the user the exact amount of excitation.

Referring back to FIG. 7, the CPU 91 or processor is also programmed sothat an individual ultrasound system having particular characteristicscan be programmed to accommodate the particular mechanical motionmechanism being utilized. Thus, the frequency of operation of thevariable generator 92 is a function of the particular system which isbeing utilized. The user, for example, will enter the name of thecolorflow system in use and the CPU 91 is programmed to contain thespecifications of the colorflow system so that it can display the propersettings for the needle detection, as for example the proper pulserepetition rate and the velocity color map to be used for optimalvisualization at the vibratory driving frequency. The resonant structuredescribed can also be incorporated into alternate structures known asneedle guides to guide needles along predetermined paths shown on thescreen of the imaging system. Thus, a VIBER mechanism 40 which is builtinto a particular guide could add visualization to the present guidingfunctions. Hence, the use of flexural-waves to produce the small motionsrequired to display the position of an interventional medical device incolor for colorflow ultrasound imaging systems has many advantages. Itis thus understood that the excitation of flexural waves in needles orother structures can be implemented by other means. In any event, onecan employ end driven flexural waves developed on solid core guide wiresand flexural waves can be produced on cannulas by driving the stylet sothat different needle cannulae can be driven by a stylet equipped with aflexural wave driver. These drivers can be piezoelectric devices whichcan be incorporated to produce flexural waves in various other guidingsystems.

Thus, many alternate embodiments, as well as additional embodiments willbecome apparent to those skilled in the art to enable the generation offlexural waves to enable the color ultrasound imaging system to respondto such waves to provide a indication to a physician or other user ofthe ultrasound system as to the location of the needle or other deviceto which the VIBER device is located on.

What is claimed is:
 1. A vibrator (mechanism) apparatus for use with anultrasound imaging system including signal processing means fordetecting motion and including display means for displaying a structuralimage of an interior region of a body in which said motion isrepresented, said vibrator adapted to be positioned on an interventionalmedical device employed by a user of said imaging system to place andmove said device within the interior of said body for observing areas ofsaid interior, comprising:a annular vibrator member having a peripheralslot, with one side of said slot contiguous with a depending armextending towards an inner surface of said member and having a largermass at the end of said arm closest to said surface to form a pendulumlike structure, with said other end of said slot contiguous with avibratable wall which when vibrated causes vibrations to couple to saiddepending arm to cause said arm to vibrate about at least one of theaxis, which vibrations are capable of propagating flexural waves, andmeans positioned on said depending arm adapted to accommodate saidmedical interventional device to cause said device when coupled to saidvibrator member to exhibit flexural wave motions, whereby said motioncan be detected by said ultrasound imaging system transducer meanscoupled to said wall to vibrate said wall at a given frequency to causesaid depending arm to vibrate at at least one frequency.
 2. The annularvibrator member according to claim 1, wherein said depending arm of saidannular member vibrates in at least one plane.
 3. The annular vibratormember according to claim 2, wherein the frequency of vibration in eachof said at least one plane is different and non-harmonically related. 4.The annular vibrator member according to claim 3, wherein saidinterventional medical device is a needle having a cannula, with saidmeans positioned on said depending arm including a spring wire clip forencircling a portion of said needle to couple said annular memberthereto.
 5. The annular vibrator member according to claim 4, whereinthe frequency of vibration about said at least one axis is a function ofsaid annular member, said cannula and said interior of said body, withthe maximum amplitude of vibration occurring at resonance.
 6. Theannular vibrator member according to claim 5, including detecting meansresponsive to said frequency of vibration to provide a control signalindicative of the frequency and amplitude of said vibration and meansresponsive to said control signal to excite said transducer means at afrequency near resonance independently of the position of said needle asmoved by said user in said body.
 7. The annular vibrator memberaccording to claim 1, wherein said transducer means is a piezoelectrictransducer.
 8. The annular vibrator member according to claim 1, whereinsaid transducer means is a magnetic transducer.